Radiological imaging system with improved internal movement

ABSTRACT

A radiological imaging system including a bed and a load-bearing structure supporting the bed. A free chamber is defined between a base of the load-bearing structure and the bed. The system also includes a gantry defining a main axis of expansion, and the gantry has a source suitable to emit radiation and a detector with a sensitive surface suitable to detect the radiation. The gantry also includes a casing having a cross-section large enough to surround the source and detector. In one embodiment, the gantry includes a rest configuration in which the casing is housed partially in the free chamber. The gantry may also include a working configuration in which the gantry at least partially extends around the bed.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. patent application Ser. No.14/800,659, filed Jul. 15, 2015, and claims the benefit to ItalianApplication No. MI2014A001297, filed Jul. 16, 2014, which is hereinincorporated by reference in its entirety.

FIELD

The present disclosure relates in general to the field of a radiologicalimaging system, and in particular, to a system and method for providinga radiological imaging system useful in the medical/veterinary sphere toobtain images of at least a portion of the internal anatomy of a patientand thus, perform analyses, diagnoses, or other assessments of thepatients.

BACKGROUND

As is known, the radiological imaging devices currently available on themarket have a standard structure including a bed on which the patient isplaced in order to perform image scanning of the patient. Theradiological imaging device includes a gantry, which houses a source foremitting X-rays and a detector for receiving the X-rays.

Given the need to contain the source, the detector and the movementsystem, the gantry is cumbersome and, in particular, has a diameter ofat least 1.5 meters and cannot therefore be maneuvered through doors orother passages present in a hospital. For that reason, if radiologicalimaging needs to be performed to verify the successful outcome of anoperation, the patient must be lifted from the operating table, placedon a bed, moved to another part of the hospital to the room where theimaging device is installed, lifted again and then placed on the bed ofthe radiological imaging device. This procedure may be furthercomplicated if the radiological imaging reveals the need for furthersurgery, in which case, the patient would need to be taken back to theoperating room. Additionally, such maneuvers often entail problems forthe patient and therefore need to be performed with particular care andexpertise. Consequently, the length of time needed to perform theaforementioned maneuvers increases.

SUMMARY

Existing limitations associated with the foregoing, as well as otherlimitations, can be overcome by a method for operating a radiologicalimaging device, and by a system, apparatus, and computer program thatoperates in accordance with the method. Briefly, and in general terms,the present disclosure is directed to various embodiments of aradiological imaging system.

A radiological imaging system with a bed, a gantry, and the method ofoperating thereof are disclosed. In one embodiment, the radiologicalimaging system permits the patient to be maneuvered easily and reducesrisks to the patient. Also, the system may permit a reduction in themaneuvers involving the patient. The radiological imaging system mayfurther permit different analyses/operations to be performed on thepatient conveniently and quickly.

According to one embodiment, a radiological imaging system, includes abed and a load-bearing structure supporting the bed. The system alsoincludes a gantry defining a main axis of expansion. The gantry has asource suitable to emit radiation and a detector with a sensitivesurface suitable to detect the radiation. The gantry also has aninternal inner guide suitable to rotate the detector around the mainaxis of expansion defining an inner sliding trajectory, and an internalouter guide suitable to rotate the source around the main axis ofexpansion defining an outer sliding trajectory. In one embodiment, thedistance from the source to the main axis of expansion is greater thanthe distance from the detector to the main axis of expansion. The gantryalso includes a casing housing the source, the detector, the internalinner guide, and the internal outer guide.

In one embodiment, the distance from the source to the main axis ofexpansion is between about 900 mm and about 480 mm, and the distancefrom the detector to the main axis of expansion is between about 600 mmand about 300 mm. These distances may vary by ten percent.

By way of example only, the casing may include a fixed arched module, afirst mobile arched module, and a second mobile arched module. Thesystem may also include at least one kinematic expansion mechanism. Thekinematic expansion mechanism is connected to the gantry and able tomove the first and second mobile arched modules with respect to thefixed arched module of the casing and vary the angular extension of thecasing and the gantry. In this example, the radiological imaging systemmay include a rest configuration in which the first mobile arched moduleis overlapping the fixed arched module so that the angular extension ofthe casing is substantially equal to the angular extension of the fixedarched module. The radiological imaging system may also include aworking configuration wherein the first mobile arched module at leastpartially protrudes from the fixed arched module so that the angularextension of the casing is greater than the angular extension of thefixed arched module. The rest configuration and working configuration ofthe system may have multiple configurations.

In yet another embodiment, the internal inner guide includes an innerarched guide integral with the first mobile arched module and definingthe inner sliding trajectory. There is at least one inner cartconstrained to the detector to move the detector along the inner archedguide. In this embodiment, the internal outer guide includes an archedouter guide integral with the second arched mobile module and definingthe outer sliding trajectory. There also is at least one outer cartconstrained to the source and adapted to move the source along the outerarched guide. The inner and outer arched guides may have an angularextension between about 180° and about 210°. The inner arched guide maybe bound to the first mobile arched module defining a first protrudingportion, and the outer arched guide is bound to the second mobile archedmodule defining a second protruding portion. In one embodiment, thefirst protruding portion has an angular extension of about 90° and thesecond protruding portion has an angular extension between about 10° andabout 20°. The angles describe herein may vary by up to ten percent.

In one embodiment, the radiological imaging system includes acompensating member arranged between the gantry and the load-bearingstructure. The compensating member may be suitable to define anadditional rotation of the source and the detector around the main axisof expansion. In one example, the angular extension of the additionalrotational plus the angular extension of the rotation of the source andthe detector defined by the internal movers is equal to about 360°.Also, the angular extension of the additional rotation of the source andthe detector may be about 180°.

Other features and advantages will become apparent from the followingdetailed description, taken in conjunction with the accompanyingdrawings, which illustrate by way of example, the features of thevarious embodiments.

BRIEF DESCRIPTION OF THE DRAWING

The teachings claimed and/or described herein are further described interms of exemplary embodiments. These exemplary embodiments aredescribed in detail with reference to the drawings. These embodimentsare non-limiting exemplary embodiments, in which like reference numeralsrepresent similar structures throughout the several views of thedrawings, and wherein:

FIGS. 1a-1e show, in perspective, an exemplary radiological imagingsystem in a possible operating sequences;

FIGS. 2a-2c are front views of part of the operating sequence of FIGS.1a -1 e;

FIGS. 3a and 3b shows one embodiment of an assembly of the radiologicalimaging system;

FIGS. 4a and 4b show an embodiment of a subassembly of the system; and

FIG. 5 shows another subassembly of the system.

DETAILED DESCRIPTION

Each of the features and teachings disclosed herein can be utilizedseparately or in conjunction with other features and teachings toprovide a radiological imaging system occupying a reduced space.Representative examples utilizing many of these additional features andteachings, both separately and in combination are described in furtherdetail with reference to the attached figures. This detailed descriptionis merely intended to teach a person of skill in the art further detailsfor practicing aspects of the present teachings and is not intended tolimit the scope of the claims. Therefore, combinations of featuresdisclosed above in the detailed description may not be necessary topractice the teachings in the broadest sense, and are instead taughtmerely to describe particularly representative examples of the presentteachings.

In the description below, for purposes of explanation only, specificnomenclature is set forth to provide a thorough understanding of thepresent disclosure. However, it will be apparent to one skilled in theart that each of these specific details are not required to practice theteachings of the present disclosure.

Moreover, the various features of the representative examples may becombined in ways that are not specifically and explicitly enumerated inorder to provide additional useful embodiments of the present teachings.It is also expressly noted that all value ranges or indications ofgroups of entities disclose every possible intermediate value orintermediate entity for the purpose of original disclosure. It is alsoexpressly noted that the dimensions and the shapes of the componentsshown in the figures are designed to help to understand how the presentteachings are practiced, but not intended to limit the dimensions andthe shapes shown in the examples. In this document, measurements,values, shapes, angles, and geometric references (such asperpendicularity and parallelism), when associated with words like“about” or other similar terms such as “approximately” or“substantially,” should be construed to allow for measurement errors orothers errors due to production and/or manufacture process, and may varyby up to ten percent.

With reference to FIGS. 1a -5, reference numeral 1 denotes theradiological imaging system.

The radiological imaging system 1 is useful in both the medical andveterinary applications for performing radiological imaging of at leastone portion of the internal anatomy of a patient. In particular, theradiological imaging system 1 is useful for performing X-rays, CT scans,fluoroscopy and other radiological imaging examinations.

In one embodiment, the radiological imaging system 1 includes a controlunit 1 a (shown in FIG. 1e ) suitable to control the functioning of theradiological imaging system 1. The system also includes a bed 20extending along a main direction (or main axis of extension) 20 a andhaving a support surface 20 b to support the patient. The systemincludes a gantry 30 suitable to perform the radiological imaging of atleast a portion of the patient and defining a main axis of expansion 30a. The gantry may have a circular trajectory of expansion 30 b, in apositioning plane 30 c having, appropriately, its center on the axis ofexpansion 30 a. The system also may include a load-bearing structure 40suitable to support the gantry 30 and, in a raised position, the bed 20and defining a free chamber 40 a. The gantry in this embodiment is acollapsible gantry.

As best shown in FIGS. 1a-1c , the bed 20 extends along a main direction(or main axis of extension) 20 a substantially parallel and, inparticular, coinciding with the main axis of expansion 30 a. Thesupporting surface 20 b may be substantially parallel to the main axisof expansion 30 a and, in particular, arranged to lie almost parallel tothe support surface of the radiological imaging system 1.

In one embodiment, the control unit 1 a may be connected to the othercomponents of the system 1 by wireless connection and/or by a cable 1 bas shown in FIG. 1e . The control unit 1 a may control and command theradiological imaging system 1. More specifically, the control unit 1 amay control the gantry 30 and its movements. The control unit 1 a mayinclude a command board able to automatically control and command theradiological imaging system 1 and any interface components (e.g., touchscreen, keyboard, joystick, etc.) suitable to allow the operator tocommand the radiological imaging system.

As shown in the examples of FIG. 1, the load-bearing structure 40includes a base 41 that comes in contact with the floor and is suitableto support the gantry 30. Also in this example is at least one column 42suitable to support the bed 20 in the raised position with respect tothe base 41. There may be two columns 42 to support the bed. However,additional columns may be included to support the weight of the bed andthe patient. In one embodiment, the system includes movement wheels 43,preferably pivoting, suitable to be arranged between a floor surfaceupon which the system 1 is disposed and the base 41 to allow themovement of the system 1 and at least one actuator 44 suitable to movethe bed 20 with respect to the base 41. Multiple actuators may be usedto move the bed.

As shown in the exemplar figures, the base 41 and the at least onecolumn 42 limit and define the chamber 40 a. In detail the chamber 40 ais delimited at the bottom (closed to the floor) by the base 41; along aside face by the column 42; if present, along a second side faceopposite to the first by the second column 42; and, optionally, the topby the bed 20.

The actuators 44 are arranged between the bed 20 and each column 42 tomodify the extension of the chamber 40 a via a translational movementsubstantially perpendicular to the main direction (or axis of extension)20 a. Alternatively, the actuators 44 modify the internal chamber 40 athrough a rotational movement of the bed 20 about an axis substantiallyparallel to the main direction 20 a.

Arranged between the base 41 and the gantry 30, the radiological imagingsystem 1 includes a rotation mechanism 50 suitable to rotate the gantry30 about an axis of rotation 50 a in one embodiment. The system may alsoinclude a translation mechanism 60 suitable to move the gantry 30 alongan axis of translation 60 a substantially parallel to the main direction20 a (FIG. 1e ).

The translation mechanism 60 is arranged between the base 41 and thegantry 30 and includes a linear guide 61. The linear guide 61 may bemotorized and suitable to control the translation along the axis oftranslation 60 a. The translation mechanism may also allow thetranslation along the axis of translation to be done manually. In thisexample, the translation mechanism 60 includes a carriage 62 connectedto the gantry 30 to slide along the linear guide 61 thus translating thegantry 30.

By way of example, the rotation mechanism 50 is arranged between thetranslation mechanism 60 and the gantry 30 and suitable to rotate thegantry 30 with respect to an axis of rotation 50 a substantiallytransverse and, in particular, substantially perpendicular to the mainaxis of extension 20 a.

In one embodiment, the rotation mechanism 50 includes a fixed plate 51suitable to be connected to the carriage 62, and a mobile plate 52connected to the gantry 30. In this embodiment, the rotational mechanism50 may also include pins, bearings or other similar elements definingthe axis of rotation 50 a. A control lever 53 suitable to be held by theoperator may permit the operator to manually control the rotation, aboutthe axis of rotation 50 a, of the mobile plate 52 and, thus, of thegantry 30 with respect to the fixed plate 51. As an alternative to thecontrol lever 53, the rotation mechanism 50 can include a motor suitableto control the rotation of the gantry 30.

In one example, the control lever 53 is suitable to be connected toholes provided in the plates 51 and 52 so as to define, for the gantry30, a first rotational blocked position in which the main direction (oraxis of expansion) 30 a, is substantially parallel to the main direction(or axis of extension) 20 a, and the circular trajectory of expansion 30b and the positioning plane 30 c are substantially perpendicular to themain direction 20 a. A second rotational blocked position in which themain axis of expansion 30 a is substantially perpendicular to the maindirection 20 a, the circular trajectory of expansion 30 b, and thepositioning plane 30 c are substantially parallel to the main direction20 a. In another example, the lever 53 may additionally define a thirdrotational blocked position in which the main axis of expansion 30 a issubstantially parallel to the axis of extension 20 a, and the circulartrajectory of expansion 30 b and the positioning plane 30 aresubstantially perpendicular to the main direction 20 a, but the gantry30 is rotated by 180° with respect to the first position.

By way of example only, and not by way of limitation, the gantry 30,rotatable by virtue of the rotation mechanism 50, includes a source 31suitable to emit radiation, such as X-rays, and defining a central axisof propagation 31 a preferably substantially perpendicular to the maindirections 20 a and 30 a. The gantry also includes a detector 32suitable to receive the radiation after it has traversed the patient'sbody and the bed 20. There may also be at least one internal mover ableto rotate the source 31 and the detector 32 around the main direction(axis of expansion) 30 a defining, for the detector 32, an inner slidingtrajectory 33 a and, for the source 31, an outer sliding trajectory 34 adistinct from the inner trajectory 33 a. In one embodiment, the gantryalso includes a casing 35 suitable to house the source 31, the detector32, and the movers. In one example, the source, detector, and movers arelocated within the casing of the gantry regardless of the configurationof the system.

The radiological imaging system 1 is useful in both the medical andveterinary applications for performing radiological imaging of at leastone portion of the internal anatomy of a patient. In particular, theradiological imaging system 1 is suitable for performing X-rays, CTscans, fluoroscopy and other radiological imaging examinations. Thus, inone embodiment, the detector 32 may have a first sensor 32 a, suitableto selectively carry out tomography or fluoroscopy and defining a firstsensitive surface 32 b suitable to detect the radiation. A second sensor32 c may be suitable to perform X-rays and define a second sensitivesurface 32 d suitable to detect the radiation. In one embodiment, thedetector may include a movement apparatus suitable to move the firstsensor 32 a and the second sensor 32 c in relation to the source 31. Ithas been contemplated other arrangements of various sensors of thedetector can be used, the embodiment described is merely one example.

By way of example only, and not by way of limitation, the first sensor32 a may include a flat panel, while the second sensor 32 c may includeat least one linear sensor. In another example, the first sensor 32 aincludes two linear sensors, positioned alongside each other anddefining substantially coplanar second sensitive surfaces 32 d.Alternatively, the second sensor 32 c may include one or morerectangular sensors or other sensors. In other embodiments, other typesof sensors can be used for sensors 32 a and 32 c and the second sensor32 c may include more or less than two sensors. It has also beencontemplated that the second sensor 32 c may include one or morerectangular sensors or other sensors.

In yet another embodiment, the detector 32 may envisage a third sensor,not shown in the drawing, preferably consisting of a direct photoniccounting sensor.

The movement apparatus is suitable to move the sensors 32 a and 32 c inrelation to the source 31 defining a first active configuration whereinonly the first sensor 32 a is able to receive the radiation emitted bythe source 31 and a second active configuration wherein only the secondsensor 32 c is able to receive the radiation.

In one embodiment, the movement device moves the detectors 32 a and 32 cin such a way that, in each of the active configurations the sensitivesurfaces 32 b and 32 d are substantially perpendicular to the axis ofpropagation 31 a so that the distance of the source 31 from thedetectors 32 a and 32 c, and more specifically, from the surfaces 32 band 32 d is kept unvaried.

Furthermore, in the embodiment in which the detector 32 envisages thethird sensor, the movement apparatus moves the three sensors, in thesame way as described below, defining a third active configurationwherein only the third sensor is able to receive the radiation emittedby the source 31. In this embodiment, the sensitive surface of the thirdsensor is substantially perpendicular to the central axis of propagation31 a. The distance of the source 31 from the third sensor and morespecifically from its sensitive surface is equal to that defined by thesource 31 and by the other surfaces 32 b and 32 d in the other activeconfigurations.

As shown in FIGS. 4a and 4b , the movement apparatus may include aload-bearing body 32 e suitable to support the detectors 32 a and 32 cand a motor 32 f. The motor may be an electric motor, or any type ofmotor suitable to rotate the detectors 32 a and 32 c along an axis ofrotation 32 g. In one embodiment the detectors 32 a and 32 c are rotatedsubstantially perpendicular to the axis of propagation 31 a. Thedetectors 32 a and 32 c may be rotated substantially parallel to orperpendicular to the main direction 20 a.

In one example, the amplitude of rotation of the detectors 32 a and 32 cis substantially equal to 90° or to 180° so that, in the first activeconfiguration (FIG. 4a ), the first surface 32 b is substantiallyperpendicular to the central axis of propagation 31 a, and the secondsurface 32 d is substantially parallel to the central axis ofpropagation 31 a. In the second active configuration (FIG. 4b ), thefirst surface 32 b may be substantially parallel to the central axis ofpropagation 31 a, and the second surface 32 d may be substantiallyperpendicular to the central axis 31 a. In this embodiment, the distancefrom the source 31 is the same as that between the source and the firstsurface 32 b in the previous configuration.

In the embodiments shown, the casing 35 forms the outer body of thegantry 30 and, therefore, it defines the dimensions and, in particular,the angular extension of the gantry 30.

By way of example, the casing 35 and, therefore, the gantry 30 may betelescopic to vary in extension along the circular trajectory ofexpansion 30 b. The telescopic casing defines, for the radiologicalimaging system 1, at least one rest configuration and at least oneworking configuration. The system may have multiple rest configurationsand working configurations that may vary by degree.

In one example of the rest configuration (FIGS. 1a and 2a ), the casing35 and the gantry 30 are contracted and have minimal angular dimensions.Therefore, in this rest configuration, the casing 35, the gantry 30, andthe positioning plane 30 c, define an arc of a circumferencesubstantially centered on the main direction (axis of expansion) 30 aand having an angular extension of, for example, approximately less than270°. In one embodiment, the arc of a circumference has an angularextension of approximately less than 240° and, in another embodiment,less than about 210° and, in yet another embodiment, approximately equalto about 190°.

Furthermore, in the rest configuration, the gantry 30 and the trajectoryof expansion 30 b define a positioning plane 30 c substantially parallelto the main direction 20 a. In one embodiment, the gantry 30 is housedin the free chamber 40 a thereby reducing the overall dimensions of thedevice 1 to a minimum and, as a consequence, leaving the support surface20 b substantially clear and easily accessible from any point. In oneembodiment, the gantry 30 is entirely housed in the free chamber 40 awhen in the rest configuration, and in another embodiment, the gantry 30is at least partially housed in the free chamber 40 a when in the restconfiguration.

As an example, in the at least one working configuration, as shown inFIGS. 1c-1e and 2c , the casing 35 and the gantry 30 have an angularextension greater than that of the rest configuration to at leastpartially surround a portion of the bed 20 and of the patient on the bed20. Additionally, the casing 35 and the gantry 30, are rotated withrespect to the rest configuration using the rotation mechanism 50, inorder to place the positioning plane 30 c substantially transverse tothe main direction (or axis) 20 a. In this example, the casing 35 andthe gantry 30 are rotated, with respect to the rest configuration, of anangle of approximately 90° and the plane 30 c is almost perpendicular tothe main direction 20 a and the axis 30 a is approximately parallel tothe main direction 20 a.

In addition to the above exemplary configurations, the radiologicalimaging system 1 may also define at least one supplementary workingconfiguration in which the casing 35 and the gantry 30 have an angularextension substantially analogous to that of the aforementioned workingconfiguration and the positioning plane 30 c is substantiallyperpendicular to the main direction 20 a, but rotated by approximately180°, around the axis of rotation 50 a, with respect to the workingconfiguration so that the gantry 30 faces an opposite direction from theworking configuration.

In one embodiment, the radiological imaging system 1 defines anotherworking configuration of maximum extension (FIGS. 1d-1e and 2c ) and,additionally, a supplementary working configuration of maximum extensionin which the casing 35 and the gantry 30 are substantially closed. Inthis embodiment, the casing 35 and the gantry 30 have an angularextension and an expansion trajectory circular 30 b of substantially360°.

In certain embodiments, the casing 35 includes at least two moduleshaving a preferred trajectory of extension that substantially coincideswith the circular trajectory 30 b and having cross-sections of differentextensions to enable a reciprocal insertion.

In one embodiment, the casing 35 includes a fixed arched module 35 asuitable to be connected to the rotation mechanism 50. The casing 35also includes at least one mobile arched module having a lessercross-section than the fixed module 35 a to be housed therein. In oneembodiment, the casing 35 includes two mobile arched modules, and thesetwo mobile arched modules may be housed within the fixed module 35 a.There may also be at least one kinematic expansion mechanism 35 bsuitable to move the at least one mobile arched module with respect tothe fixed module 35 a along the circular trajectory of expansion 30 b toallow the casing 35 to assume any angular extension between 360° and theangular extension of the fixed arched module 35 a.

By way of example, the casing 35 may include a fixed arched module 35 a,a first mobile arched module 35 c disposed at an end of the fixed module35 a, a second mobile arched module 35 d disposed at the opposite end ofthe fixed arched module 35 a. The first and second mobile arched modulesmay be substantially symmetrical. In this example, the system mayinclude a kinematic expansion mechanism 35 b able to move, independentlyfrom each other, the first and second mobile arched modules 35 c and 35d with respect to the fixed module 35 a along the trajectory of circularexpansion 30 b. The movement of the first mobile arched module 35 c isin the opposite direction of the second mobile arched module 35 d sothat at maximum extension, the first and seconds mobile arched modules35 c and 35 d reach a mutual contact point.

In one embodiment, the fixed module 35 a and mobile arched modules 35 cand 35 d have substantially the same expansion axis almost coincidingwith the trajectory of circular expansion 30 b.

The first and second mobile arched modules 35 c and 35 d may have across-section different from that of the fixed module 35 a to at leastpartially overlap the fixed module 35 a. In another embodiment, thecross-section of the mobile arched modules is the same as thecross-section of the fixed module. In one example, the mobile modules 35c and 35 d may have a cross-section smaller than that of the fixedarched module 35 a to be housed inside the fixed arched module.

In one embodiment, the kinematic expansion mechanism 35 b is adapted tomove the mobile arched modules 35 c and 35 d with respect to the fixedmodule 35 a to vary the extension of the portion of each mobile archedmodule superimposed and, in particular, included in the fixed archedmodule 35 a.

In one example, the kinematic expansion mechanism 35 b is adapted toarrange, in the rest configuration (FIGS. 1a and 2a ), each mobilearched module 35 c and/or 35 d totally located inside in the fixedmodule 35 a so that the angular extent of the gantry 30 is substantiallyequal to that of the fixed module 35 a. In the rest configuration ofthis example, the mobile arched modules 35 c and 35 d are totally insidethe fixed module 35 a of the casing 35 and may be substantially incontact with each other.

In one embodiment, in the at least one working configuration (FIGS. 1dand 2c ) and, if provided, in the at least one supplementary workingconfiguration, the kinematic expansion mechanism 35 b may allow each ofthe mobile arched modules 35 c and 35 d to protrude from the fixedmodule 35 a so that the angular extent of the gantry 30 is greater thanthe one of the fixed module 35 a and, almost equal to that of the fixedmodule 35 a plus the angular extent of the portion of each mobile module35 c and 35 d protruding from the fixed module 35 a.

In one embodiment, the kinematic mechanism 35 b (FIG. 5) is mechanicaland, for example, includes at least one rack 35 e disposed on eachmobile arched module 35 c and 35 d and extending along the circulartrajectory of expansion 30 b. The kinematic mechanism 35 b may alsoinclude at least one motorized toothed wheel 35 f hinged to the fixedarched module 35 a, engaging with the racks 35 e to control the motionof the mobile arched modules 35 c and 35 d along the trajectory 30 b.

Alternatively, the kinematic mechanism 35 b may move each mobile archedmodule 35 c and 35 d with respect to the fixed arched module 35 athrough belts, arched actuators, or, in a further alternative, it can beof magnetic type. In a separate embodiment, the mobile arched modules 35c and 35 d are manually moved with respect to the fixed arched module 35a. There may be no kinematic mechanism 35 b in this specific embodiment.

In order to store the kinematic expansion mechanism 35 b between themodules 35 a, 35 c and 35 d, each mobile arched module 35 c and 35 d isprovided with a recess defining a housing channel 35 g for the kinematicexpansion mechanism 35 b.

In one embodiment, the source 31 and the detector 32 and the one or moreinternal movers may have an angular extension below the angularextension of the fixed module 35 a.

In an exemplary embodiment, in order to move the source 31 and thedetector 32 in an independent manner, the gantry 30 includes an internalinner mover 33 defining, for the detector 32, an inner slidingtrajectory 33 a and an internal outer mover 34 defining, for the source31, an outer sliding trajectory 34 a distinct from the outer slidingtrajectory 33 a.

The inner and outer sliding trajectories 33 a and 34 a may have acircular shape with its center on the axis 30 a to move the source 31and/or the detector 32 without substantially changing its distance fromthe main axis of expansion 30 a. In one example, the inner and outersliding trajectories 33 a and 34 a lie on a single plane substantiallyperpendicular to the main axis of expansion 30 a and substantiallyparallel to the positioning plane 30 c.

In one exemplary embodiment, the outer sliding trajectory 34 a defines adistance from the source 31 to the main axis of expansion 30 a, and theinner sliding trajectory 33 a defines a distance of the detector 32,i.e. the sensitive surfaces 32 b or 32 d, from the main axis ofexpansion 30 a. The radius defined by the outer sliding trajectory 34 ais greater than the radius defined by the inner sliding trajectory. Ithas been contemplated that the outer sliding trajectory 34 a defines adistance of the source 31 from the main axis of expansion 30 a betweenabout 1100 mm and about 300 mm. This distance may also be between about900 mm and about 480 mm. In this example, the inner sliding trajectory33 a defines a distance of the sensitive surface of the detector 32 fromthe main axis of expansion 30 a between about 900 mm and about 150 mmand, in detail, between about 600 mm and about 300 mm.

By way of example only, each internal mover 33 and 34 may include anarched guide and at least one cart adapted to move it along the archedguide.

In one embodiment, best shown in FIGS. 3a and 3b , the internal innerguide 33 includes an inner arched guide 33 b integral with the firstmobile module 35 c and defining the sliding trajectory 33 a. Theinternal inner guide 33 also may include at least one inner cart 33 c.The inner cart 33 c may be motorized (electric) and preferably ofrecirculating ball type, although any suitable motor may be used. Inthis embodiment, the inner cart 33 c may be constrained to the detector32 and adapted to move it along the inner arched guide 33 b and,therefore, along the inner trajectory 33 a. The internal outer guide 34may include an arched outer guide 34 b integral with the second mobilearched module 35 d and defining the sliding trajectory 34 a. Theinternal outer guide 34 also may include at least one outer cart 34 c.As with the inner cart 33 c, the outer cart 34 c may be motorized(electric) and preferably of recirculating ball type, although anysuitable motor may be used. In this embodiment, the outer cart 34 c maybe constrained to the source 31 and adapted to move it along the outerarched guide 34 b and, therefore, along the outer trajectory 34 a.

In certain embodiments, an opening or slot may be disposed on eachmobile arched module 35 c and 35 d, duplicating the guides 33 b and 34b. Also in certain embodiments, a rack can be disposed on the archedguide 33 b and 34 b, on the side opposite to the inner and outer carts33 c and 34 c. Further, the toothed wheel of the kinematic mechanism 35b may engage, through the opening or slot, the rack to control themotion of the mobile arched modules 35 c and 35 d by acting on thecurved guide 33 b and 34 b.

In one embodiment, each arched guide 33 b and 34 b has an angularextension at least equal to 180° so that the internal movers 33 and 34are able to rotate the detector 32 and source 31, respectively, by anangle between about 0° and about 180°. It has been contemplated that thearched guides 33 b and 34 b have an angular extension between about 180°and about 210°. In another embodiment, the arched guides 33 b and 34 bhave an angular extension between about 190° and about 200°.

By way of example only, the inner arched guide 33 b may be jointly boundto the first mobile arched module 35 c so as to define, on oppositesides of and with respect to the first module 35 c, a first innerprotruding portion 33 d and a second inner protruding portion 33 e. Inthe rest configuration (FIG. 3a ), the first inner portion 33 d may besuperimposed to the second mobile module 35 d and the second innerprotruding portion 33 e may be cantilevered with respect to the mobilearched modules 35 c and 35 d. Also, in the working configuration ofmaximum extension (FIG. 3b ), the first inner protruding portion 33 dmay be cantilevered with respect to the mobile arched modules 35 c and35 d and the second inner protruding portion 33 e may be superimposed tothe second mobile arched module 35.

In one example, the outer arched guide 34 b is jointly bound to thesecond mobile module 35 d to define, on opposite sides of and withrespect to the module 35 d, a first outer protruding portion 34 d and asecond outer protruding portion 34 e. In the rest configuration (FIG. 3a) of this example, the first outer portion 34 d may be superimposed tothe first mobile module 35 c and the second outer protruding portion 34e may be cantilevered with respect to the mobile arched modules 35 c and35 d. Also, in the working configuration of maximum extension (FIG. 3b), the first outer protruding portion 34 d may be cantilevered withrespect to the mobile arched modules 35 c and 35 d and the second outerprotruding portion 34 e may be superimposed to the first mobile module35 c.

In one embodiment, the first protruding portions 33 d and 34 d and thesecond protruding portions 33 e and 34 e respectively may have anangular extension equal to about 90° and about 10° to about 20°.

In certain embodiments, the internal movers 33 and 34 may move, thesource 31 and the detector 32 with the guides 33 b and 34 b along thetrajectories 33 a and 34 a by an angle between about 0° and about 180°or at least about 360°, with respect to the mobile arched modules 35 cand 35 d. Therefore, each mover 33 and 34 may include a control groupadapted to move, along the sliding trajectory 33 a and 34 a, the archedguide 33 b and 34 b relative to the casing 35 and, the mobile modules 35c and 35 d.

In one embodiment, the control group defines for each internal mover 33and 34 a contracted condition, in which the inner arched guide 33 b andthe outer arched guide 34 b are respectively substantially superimposedto the first mobile module 35 c and to the second module 35 d, and anexpanded condition in which the arched guide 33 b and 34 b protrudes atleast partially from the corresponding mobile module 35 c and 35 d.

In one embodiment, the control group is adapted to move the arched guide33 b or 34 b by way of a magnetic field and it includes a magnet, fixedon the mobile module 35 c and/or 35 d, suitable to control the archedguide 33 b or 34 b interacting with permanent magnets connected to thearched guide 33 b or 34 b. Alternatively, the control group is adaptedto mechanically move the arched guide 33 b or 34 b and it may include amotorized toothed wheel hinged, preferably, to the arched guide 33 b or34 b and suitable to engage with a rack obtained on the mobile archedmodule 35 c and/or 35 d.

In this embodiment, the arched guide 33 b and 34 b may have angularextension almost between 90° and 110°.

In certain embodiments, the internal movers 33 and 34 can be oftelescopic type and, therefore, able to move, of an angle between about0° and about 180°, the source and detector by a variation of theirangular extension along the trajectory 33 a and 34 a. Therefore, eachmover 33 and 34 may include an additional arched guide extending almostalong the trajectory 30 b and interposed between the arched guide 33 bor 34 b and the cart 33 c or 34 c to allow the cart 33 c and 34 c toslide on the additional arched guide. The control group may be adaptedto vary the extension of the internal mover 33 or 34, along the slidingtrajectory 33 a and 34 a, by moving one of the additional arched guidesrelative to the corresponding arched guide 33 b and 34 b and, therefore,to the casing 35.

In this embodiment, the control group of each guide 33 and 34 defines acontracted condition, in which the additional arched guide issubstantially overlapping the corresponding arched guide 33 b or 34 band mobile module 35 c or 35 d, and an expanded condition in which theadditional arched guide protrudes at least partially from thecorresponding arched guide 33 b or 34 b and mobile module 35 c or 35 d.

Additionally, the control group defines an internal mover 33 and/or 34provided with a stroke-multiplying mechanism obtaining an output speedof greater amplitude, preferably of twice the amplitude, with respect tothe input speed. Therefore, the control group includes a rack obtainedon the mobile arched module 35 c and/or 35 d or 34 b. The control groupmay also include an additional rack obtained on the arched guide 33 b or34 b, and a motorized toothed wheel hinged to the additional archedguide. The motorized toothed wheel may be suitable to engage with bothracks determining a speed of the additional guide (output speed) havingan amplitude twice the amplitude of the input speed of the toothedwheel.

In this embodiment, each of the arched guides 33 b and 34 b and theadditional guide have substantially the same angular extension, whichmay be between about 90° and about 110°.

In certain embodiments, inside the casing 35, the gantry 30 includes asensor movement system 36 located between the detector 32 and the cart33 c of the internal inner guide 33 and able to translate the detector32 keeping sensitive surfaces 32 b and/or 32 d almost perpendicular tothe axis of propagation 31 a.

In one embodiment, the sensor movement system 36 is adapted to translatethe detector 32 along a flagging axis 36 a substantially perpendicularto the axis of propagation 31 a and, to the main axis of expansion 30 a.In one embodiment, the sensor movement system 36 is adapted to translatethe detector 32, with respect to a position in which the axis ofpropagation 31 a intersect the center of the sensitive surfaces 32 b or32 d, of a quantity between about ±400 mm and about ±50 mm, orsubstantially within about ±400 mm and about ±300 mm.

The sensor movement system 36 may include a flapping guide 36 b definingthe flapping axis 36 a, a flapping cursor 36 c supporting the detector32 and able to slide along the flapping guide 36 b, and a flapping motor36 d. The flapping motor 36 d may be an electric motor, suitable tocommand the motion of the flapping cursor 36 c along the flapping guide36 b.

In yet another embodiment, the imaging radiological imaging system 1appropriately includes a compensating member 70 arranged between thegantry 30 and the rotation mechanism 60 and suitable to rotate thegantry 30 to facilitate the complete rotation of the source 31 and ofthe detector 32 about the bed 20 and, thus, about the patient. It hasalso been contemplated that the system includes one or more integral orremovably attached cover blocks 80, preferably two, suitable to seal theends of the gantry 30 and the ends of the mobile arched modules 35 c and35 d when the system is in the closed configuration.

The compensation member 70 is suitable to rotate the source 31 and thedetector 32 about an axis substantially parallel to the main direction(or axis of extension) 20 a and, about the main axis of expansion 30 awhen the gantry 30 is at least in the first rotational blocked positionor in the third rotational blocked position. In one embodiment, theamplitude of the additional rotation is such that the amplitude ofrotation defined by the internal movers 33 and 34 plus the amplitude ofthe additional rotation defined by the member 70 allows the source 31and the detector 32 to realize at least one complete rotation around themain axis of expansion 30 a, the bed 20 and, therefore, around thepatient. The sum of the rotations is at least equal to 360° and,preferably, substantially equal to 360°.

In one embodiment, the amplitude of the additional rotation is equal toan angle between about 100° and about 220°, or between about 145° andabout 200°, or substantially equal to about 180°.

The compensating member 70 may include at least one rack 71 having atrajectory extending substantially in the shape of an arc of acircumference having its center on the main axis of expansion 30 a.Also, the compensating member 70 may include at least one motorizedtoothed wheel or other similar device suitable to engage with the rack71 to control the rotation of the gantry 30.

In one embodiment, the motorized toothed wheel is connected to themobile plate 52, whereas the rack 71 is obtained on the external surfaceof the casing 35 and, on the external surface of the fixed arched module35 a that is on the surface facing the rotation mechanism 50.

By way of example only, each cover block 80 includes a protection 81having a plate, a slat system, or other element suitable to overlap asection of the fixed module 35 a. It has been contemplated that a motor,not shown in the drawings, suitable to move the protection 81 withrespect to the ends of the mobile arched modules 35 c and 35 d and,thus, of the gantry 30, may also be present. In this embodiment, themotor is an electric motor and moves the protection 81 by means of arotational movement with respect to an axis substantially perpendicularto the positioning plane 30 c of the circular trajectory of expansion 30b.

In one embodiment, the motor is suitable to overlap the protection 81with the ends of the gantry 30, closing the gantry 30 when the system isin the rest configuration or in a working configuration characterized byan extension of the gantry 30 substantially less than 360°. The motoralso distances the protection 81 from the ends of the gantry 30 in orderto permit the correct expansion of at least the gantry 30, when thesystem 1 is in the working configuration and the gantry is substantiallyclosed, that is, when it defines a closed ring and, consequently, has anextension equal to 360° (above defined configuration of maximumextension or supplementary working configuration of maximum extension).

By way of example only, and not by way of limitation, a method of usingthe radiological imaging system will be described. In one embodiment,the radiological imaging system 1 is initially in the rest configuration(FIGS. 1a and 2a ) with the gantry 30 arranged inside the free chamber40 a and, thus, the support surface 20 b practically completely free andsubstantially accessible from any point.

In this embodiment, in the rest configuration the gantry 30 has thecasing 35 with the mobile arched modules 35 c and 35 d substantiallyhoused inside the fixed arched module 35 a and the movers 33 and 34overlapped to the fixed module 35 a or, if provided, in the contractedcondition.

The operator places the patient on the bed 20 and controls the movementinto the desired working configuration (FIGS. 1d and 2c ).

In one embodiment, the operator, using the rotation mechanism 50,rotates the gantry 30 by approximately 90° to arrange the positioningplane 30 c substantially perpendicular to the main direction (or axis ofextension) 20 a. Next, the casing 35 and the gantry 30, translate alongthe circular trajectory of expansion 30 b until assuming the desiredangular extension.

In one embodiment, should the gantry 30 become substantially closed and,thus, assume an extension of approximately 360°, each cover block 80moves the protection 81 freeing the ends of the mobile modules 35 c and35 d and of the gantry 30.

In this embodiment, during this change of configuration, the two mobilearched modules 35 c and 35 d rotate along the circular trajectory ofexpansion 30 b, with opposite directions of rotation, placing the archedguides 33 b and 34 b on opposite sides with respect to the axisprevalent 30 a (FIG. 3b ).

When the desired working configuration is reached, the operator may thenselect the portion of the body to be analysed. In one embodiment thecontrol unit 1 a instructs each of the inner and outer carts 33 c and 34c to slide along the respective arched guide 33 b and 34 b placing thedetector 32 and/or the source 31 in the desired position. Alternatively,the movement of the inner cart 33 c and/or out cart 34 c and, therefore,of the detector 32 and/or the source 31 are defined, in addition to themotion of the carts 33 c and 34 c on the respective guide, by thecontrol group above described.

If the movement of the cart 33 c and 34 c is not sufficient to reach therequired position and, therefore, to allow the angular position of thesource 31 and/or the detector 32 to be those optimal for the type ofimaging to be performed, the control unit 1 a may then activate thecompensation member 70 in order to rotate the gantry 30, thus bringingthe source 31 and/or the detector 32 in the proper position.

Now in this embodiment, either automatically or in response to a commandgiven by the operator through the control unit 1 a, the source 31 andthe detector 32 perform the desired radiological imaging.

For example, should the operator wish to carry out a tomography and/orfluoroscopy, the radiological imaging system 1 is made to pass into thefirst active configuration.

As a result, the motor 32 f rotates the sensors 32 a and 32 c, inrelation to the axis of rotation 32 g, in such a way that the firstsensitive surface 32 c is positioned substantially perpendicular to theaxis of propagation 31 a and in such a position as to be hit by theradiation emitted by the source 31.

After concluding the foregoing operations, the source 31 and thedetector 32 perform, either automatically or in response to a commandfrom the operator control using the control station 30, the radiologicalimaging procedure while the translation mechanism 60 moves the gantry 30along the axis of translation 60 a to permit the system 1 to performradiological imaging over the entire portion to be analyzed.

Should the operator wish to use the second sensor 32 c and therebyperform a different radiological imaging procedure, the operator wouldthen control the movement into the second active configuration.

As a result, the motor 32 f rotates the sensors 32 a and 32 c, inrelation to the axis of rotation 32 g, in such a way that the firstsensitive surface 32 b moves away from the position previously adopted.Moreover, the rotation positions the second sensor 32 c in such a waysecond sensitive surface 32 d, which is positioned substantiallyperpendicular to the axis of propagation 31 a and in such a position asto be hit by the radiation emitted by the source 31 and to be at thesame distance as that assumed by the first surface 32 b in relation tothe source 31 in the previous configuration.

In certain embodiments, if a 360° imaging is required, the internalmovers 33 and 34 and the member 70, during the imaging, rotate thesource 31 and the detector 32 in order to allow the 360° imaging.

When the radiological imaging procedure is complete, the operator maycontrol the return of the system 1 to the rest configuration and maythen, for example, perform surgery on the patient without removing thepatient from the device.

Alternatively, if a second radiological imaging procedure is necessary,for example involving a translation of the detector 32 in the oppositedirection, the operator controls the passage of the system 1 first intothe rest configuration and then into the supplementary workingconfiguration and then performs the second imaging procedure.

In view of the foregoing, it can be appreciated that the radiologicalimaging system 1, by virtue of varying both the extension of the gantry30 and its position in relation to the bed 20, makes it possible toperform a plurality of operations/analyses on the patient without movinghim from the bed 20.

In one embodiment, in the rest configuration, the gantry 30 ispractically entirely housed in the free chamber 40 a, so that the spaceoccupied by the system 1 is defined by the bed 20 and by theload-bearing structure 40 and is, therefore, substantially the same as ahospital bed, that is a bed normally used to transport the patient toother areas within the hospital or to perform an operation on thepatient.

Furthermore, the reduction in the overall dimensions has been achievedby displacing the internal movers 33 and 34. Additionally, the reductionin dimensions may be obtained because the internal movers 33 and 34constitute innovative arched telescopic guides characterized by a highexpansion capacity which can, in some case, permit a rotation of thebody 33 b and 34 b, and thus, of the source 31 or detector 32 with anamplitude substantially twice that of the amplitude of the input motionof the guide 33 and 34.

Additionally, the system 1, the dimensions of which, in the restconfiguration, are similar to those of an examination bed, can easily bemaneuvered inside a structure/hospital.

Unlike with the known imaging devices, the radiological imaging system 1is able to easily and readily pass through doors, in lifts or otheropenings normally present in a hospital.

Moreover, image acquisition by the imaging system 1 is versatile. Byvirtue of the internal movers 33 and 34 and the compensating member 70,the source 31 and the detector 32 can rotate by 360° so that the angleof inclination of the radiation, that is, the central axis 31 a, withrespect to the patient, can be adjusted as required.

Image acquisition by the imaging system 1 is also versatile by virtue ofthe rotation mechanism 50 which, by defining the second and the thirdrotational blocked position for the gantry 30 and, thus, two workingconfigurations for the system 1, allows the detector 32 and the linearsensor (in one example), to be used in two different image acquisitiondirections, although other types of sensors can be employed instead.

Contrary to the known devices, where images can only be acquired withthe gantry translating in a single direction, with the system 1, thegantry 30 can be rotated by about 180° so that scans can be performed inboth directions and, thus, specific radiological imaging can beperformed without having to move the patient.

Furthermore, by virtue of the cover blocks 80, which seal the ends ofthe gantry 30 when the system 1 is in the rest configuration, the entryof any blood, debris or other material that could damage the internalcomponents of the gantry 30 can be prevented.

Consequently, an innovative radiological imaging procedure is providedby virtue of the radiological imaging system 1.

With the radiological imaging procedure, the analysis is only performedwhen the patient is in the ideal condition, thus limiting exposure toradiation and the costs of the analysis.

In the case of injecting a contrast liquid, the radiological imagingprocedure allows the analysis to be performed when the liquid is in theportion of the body to be analyzed, thus avoiding the risk of a poorquality analysis due to the absence of the liquid in the portion to beanalyzed.

In at least some cases when the correct position of the patient isessential, by being able to check the position of the portion to beanalyzed before performing the radiological imaging procedure, theradiological imaging procedure is only performed when the patient is inthe desired position.

Additionally, by virtue of the radiological imaging device, theprocedure can be carried out without moving the patient during theentire procedure.

Modifications and variations may be made to the invention describedherein without departing from the scope of the inventive concept. Allthe elements as described and claimed herein may be replaced withequivalent elements and the scope of the invention includes all otherdetails, materials, shapes and dimensions.

For example, the source 31 and the detector 32 are integrallyconstrained to the gantry 30, which in one embodiment is free ofhandlers 33 and 34. In one example, the source 31 is integral with thefixed arched module 35 a or one of the mobile modules 35 c and 35 d; andthe detector 32 can be rigidly integrally with one of mobile modules 35c and 35 d or to the fixed module 35 a so as to be arranged on theopposite side to the spring 31 in one of the active configurations.

In one embodiment, the compensating member 70 defines an amplitude ofthe additional rotation substantially equal to an angle substantiallygreater than 180° and, in another embodiment, at least substantially360°.

The compensating member 70, therefore, in addition to the rack 71 andthe at least a motorized toothed wheel, presents an additional rackhaving a development trajectory substantially arc of circumferencecentered on the axis 30 a prevalent development.

In detail, to allow the closure of the mobile arched modules 35 c and 35d, the additional rack can have a different radius respect to the rack71 and, therefore, the compensating member 70 may provide asupplementary motorized toothed wheel able to engage the additional rackcommanding the rotation of the gantry 30.

One of ordinary skill in the art will appreciate that not allradiological imaging systems have all these components and may haveother components in addition to, or in lieu of, those componentsmentioned here. Furthermore, while these components are viewed anddescribed separately, various components may be integrated into a singleunit in some embodiments.

The various embodiments described above are provided by way ofillustration only and should not be construed to limit the claimedinvention. Those skilled in the art will readily recognize variousmodifications and changes that may be made to the claimed inventionwithout following the example embodiments and applications illustratedand described herein, and without departing from the true spirit andscope of the claimed invention, which is set forth in the followingclaims.

What is claimed:
 1. A radiological imaging system, comprising: a bed; aload-bearing structure connected to the bed and configured to supportthe bed, the load-bearing structure having a base that is parallel withthe bed and forming a free chamber between the base and the bed; and agantry defining a main axis of expansion and connected to theload-bearing structure, the gantry having a source configured to emitradiation and a detector with a sensitive surface configured to detectthe radiation, the gantry including a casing having a cross-sectionlarge enough to surround the source and detector, wherein the gantryincludes a rest configuration in which the casing is housed partially inthe free chamber and the gantry does not fully extend around the bed,and the gantry includes a working configuration in which the gantry atleast partially or fully extends around the bed with the main axis ofexpansion parallel to the bed.
 2. The radiological imaging system ofclaim 1, wherein the gantry includes an internal inner guide configuredto rotate the detector around the main axis of expansion defining aninner sliding trajectory, and an internal outer guide configured torotate the source around the main axis of expansion defining an outersliding trajectory, wherein the distance from the source to the mainaxis of expansion is greater than the distance from the detector to themain axis of expansion.
 3. The radiological imaging system of claim 2,wherein the casing includes a fixed arched module, a first mobile archedmodule, and a second mobile arched module.
 4. The radiological imagingsystem of claim 3, wherein the internal inner guide includes an innerarched guide integral with the first mobile arched module and definingthe inner sliding trajectory and at least one inner cart constrained tothe detector to move the detector along the inner arched guide, andwherein the internal outer guide includes an outer arched guide integralwith the second mobile arched module and defining the outer slidingtrajectory, and at least one outer cart constrained to the source andadapted to move the source along the outer arched guide.
 5. Theradiological imaging system of claim 4, wherein the inner and outerarched guides have an angular extension between about 180° and about210°.
 6. The radiological imaging system of claim 4, wherein the innerarched guide is bound to the first mobile arched module defining a firstprotruding portion, and the outer arched guide is bound to the secondmobile arched module defining a second protruding portion.
 7. Theradiological imaging system of claim 6, wherein the first protrudingportion has an angular extension of about 90° and the second protrudingportion has an angular extension between about 10° and about 20°.
 8. Theradiological imaging system of claim 2, further comprising acompensating member arranged between the gantry and the load-bearingstructure and configured to define an additional rotation of the sourceand the detector around the main axis of expansion.
 9. The radiologicalimaging system of claim 8, wherein the angular extension of theadditional rotation plus the angular extension of the rotation of thesource and the detector defined by the internal inner guide is equal toabout 360°.
 10. The radiological imaging system of claim 9, wherein theangular extension of the additional rotation of the source and thedetector is equal to about 180°.
 11. The radiological imaging system ofclaim 1, wherein in the rest configuration the casing is housedsubstantially in the free chamber.
 12. The radiological imaging systemof claim 1, wherein in the working configuration the gantry fullyextends around the bed with the main axis of expansion parallel to thebed.
 13. The radiological imaging system of claim 1, wherein the casingincludes a fixed arched module, a first mobile arched module, and asecond mobile arched module.
 14. The radiological imaging system ofclaim 13, further comprising at least one kinematic expansion mechanismconnected to the gantry and configured to translate the first and secondmobile arched modules with respect to the fixed arched module of thecasing.
 15. The radiological imaging system of claim 14, wherein in therest configuration the first mobile arched module is overlapping thefixed arched module so that the angular extension of the casing issubstantially equal to the angular extension of the fixed arched module.16. The radiological imaging system of claim 14, wherein in the workingconfiguration the first mobile arched module at least partiallyprotrudes from the fixed arched module so that the angular extension ofthe casing is greater than the angular extension of the fixed archedmodule.